Controlled cross-linking processing of proteins

ABSTRACT

A method of forming a cross-linked protein structures includes preparing a solution of protein dissolved in a benign solvent and forming an intermediate protein structure from the solution. The intermediate protein structure can be cross-linked by providing for a specific ratio of chemical cross-linking agents to form the cross-linked protein structure. The solution can be prepared by adding a cross-linker of N-hydroxysuccinimide (NHS) and 1-ethyl-3-(3-dimethylaminopropyl)carbodiimide hydrochloride (EDC) at a ratio of two-to-one of NHS to EDC to alcohol. PBS buffer (20×) can be added to the solution until the volume ratio of PBS buffer (20×) to alcohol is about one-to-one. About 16 percent by weight of protein can be dissolved in the solution. The solution can be electrospun to form an intermediate protein structure. After a period of time, the protein structure can be cross-linked to form the cross-linked protein structure.

PRIORITY CLAIM

This application is a continuation-in-part of U.S. patent applicationSer. No. 12/571,043, titled “Benign Solvents for Forming ProteinStructures,” filed on Sep. 30, 2009, which claims priority to U.S.Provisional Patent Application Ser. No. 61/194,685, titled“Electrospinning of Fiber Scaffolds,” filed on Sep. 30, 2008. Thisapplication claims priority to and the full benefit of the foregoingreferenced patent applications, which are incorporated by reference asif fully rewritten herein. This application further claims priority toand the full benefit of U.S. Provisional Patent Application Ser. No.61/467,923, titled “Kinetically Controlled Cross-Linking Processing ofProteins,” filed on Mar. 25, 2011, which is incorporated by reference asif fully rewritten herein.

STATEMENT OF GOVERNMENT INTEREST

This invention was made with government support under Grant NumberAR039750 awarded by the National Institutes of Health, NationalInstitute of Arthritis and under Grant Number EY019406 awarded by theNational Institute of Health, National Eye Institute. The government hascertain rights in the invention.

TECHNICAL FIELD

The disclosed material relates generally to forming protein structuresfrom a solution of protein dissolved in a benign solvent andcross-linking such protein structures.

BACKGROUND

Products and devices constructed from man-made materials can beimplanted into or applied onto a human body to treat injuries, diseases,and other conditions of the human body. The materials chosen for suchproducts or devices can be important for the product or device tosuccessfully treat conditions of the human body. For instance, thecompatibility of a material with the human body can determine if theproduct or device can be positioned on or in the human body. Products ordevices can be made from synthetic material. However, if the syntheticmaterial is dissimilar to human tissue, the success of the product ordevice can be limited. Products and devices constructed from naturallyoccurring materials such as proteins can provide biocompatible productsor devices for implantation into or applying onto the human body totreat conditions of the human body.

SUMMARY

A method of forming a final protein structures includes preparing asolution of protein dissolved in a benign solvent and forming anintermediate protein structure from the solution. The intermediateprotein structure is cross-linked by providing for a specific ratio ofchemical cross-linking agents to form the final protein structure.

In another method, a cross-linked protein structure is formed. Asolution is prepared by adding a cross-linker of N-hydroxysuccinimide(NHS) and 1-ethyl-3-(3-dimethylaminopropyl)carbodiimide hydrochloride(EDC) at a ratio of two-to-one of NHS to EDC to alcohol. PBS buffer(20×) is added to the solution until the volume ratio of PBS buffer(20×) to alcohol is about one-to-one. About 16 percent by weight ofprotein is dissolved in the solution. The solution is electrospun toform an intermediate protein structure. After a period of time, theprotein structure is cross-linked to form the cross-linked proteinstructure.

BRIEF DESCRIPTION OF THE DRAWINGS

Objects and advantages together with the operation of the invention maybe better understood by reference to the detailed description taken inconnection with the following illustrations, wherein:

FIG. 1 is a schematic illustration of apparatus for electrospinningprotein fibers from a protein solution;

FIG. 2A is a chart showing electrospun fiber diameter distribution;

FIG. 2B is an SEM image of an electrospun fiber scaffold;

FIG. 3A is an SEM image of an electrospun fiber scaffold;

FIG. 3B is an SEM image of an electrospun fiber scaffold;

FIG. 3C is a chart showing electrospun fiber diameter distribution;

FIG. 4A is an SEM image of an electrospun fiber scaffold;

FIG. 4B is a chart showing electrospun fiber diameter distribution;

FIG. 5A is an SEM image of an electrospun fiber scaffold;

FIG. 5B is a chart showing electrospun fiber diameter distribution;

FIG. 6 is multiple SEM images of electrospun fiber scaffolds;

FIG. 7 is an SEM image of an electrospun fiber scaffold;

FIG. 8 is a schematic illustration of apparatus for electrospinning orelectrospraying protein agglomerations from a protein solution;

FIG. 9 is an SEM image of cross-linked agglomerations;

FIG. 10 is an SEM image of cross-linked agglomerations;

FIG. 11 is an SEM image of cross-linked agglomerations;

FIG. 12A is an SEM image of a cross-linked protein film;

FIG. 12B is an SEM image of a cross-linked protein film;

FIG. 13A is an SEM image of a protein structure with an open network ofpores; and

FIG. 13B is an SEM image of a protein structure with an open network ofpores.

FIG. 14A is a graph illustrating the relationship between gelation timeand mole ratio of NHS to EDC based on rheological results.

FIG. 14B is a graph illustrating the relationship between the log ofgelation time and mole ratio of NHS to EDC based on rheological results.

FIG. 15A is a photograph of hydrated in-situ cross-linked collagen gel.

FIG. 15B is a photograph of lyophilized in-situ cross-linked collagengel.

FIG. 16A is a scanning electron microscope (SEM) image of across-section of lyophilized in-situ cross-linked collagen gel.

FIG. 16B is an SEM image of a top portion of FIG. 3 a.

FIG. 16C is an SEM image of a middle portion of FIG. 3 a.

FIG. 16D is an SEM image of a bottom portion of FIG. 3 a.

FIG. 17A is a photograph of in-situ cross-linked collagen gel formed astube-like structures.

FIG. 17B is a photograph of in-situ cross-linked collagen gel formed asa hemispheric-like structure.

FIG. 18 is a photograph of collagen gel used to print onto a glassslide.

FIG. 19A is a photograph of in-situ cross-linked collagen hydrogels withPCL-Pac mat embedding.

FIG. 19B is a photograph of in-situ cross-linked collagen hydrogels withPLEA-beta carotene macro beads.

FIG. 20A is a photograph of an electrospun in-situ cross-linked collagenfibrous scaffold in a dry state.

FIG. 20B is a photograph of an electrospun in-situ cross-linked collagenfibrous scaffold in a hydrated state.

FIG. 21A is a SEM image of electrospun in-situ cross-linked collagenfibers.

FIG. 21B is a SEM image of electrospun in-situ cross-linked collagenfibers.

FIG. 21C is a histogram of the electrospun in-situ cross-linked collagenfibers of FIG. 21A.

FIG. 21D is a graph illustrating the relationship between average fiberdiameter and electro spinning time.

FIG. 22A is an SEM image of in-situ cross-linked collagen fibers exposedto 33% relative humidity for 3 days.

FIG. 22B is an SEM image of in-situ cross-linked collagen fibers exposedto 43% relative humidity for 3 days.

FIG. 22C is an SEM image of in-situ cross-linked collagen fibers exposedto 53% relative humidity for 1 day.

FIG. 23A is a photograph of an electrospun cross-linked collagen fibrousscaffold in a dry state.

FIG. 23B is a photograph of an electrospun cross-linked collagen fibrousscaffold in a hydrated state.

FIG. 24A is an SEM image of electrospun in-situ cross-linked collagenfibrous scaffolds after water treatment.

FIG. 24B is an SEM image of electrospun in-situ cross-linked collagenfibrous scaffolds after water treatment.

FIG. 25A is an SEM image of in-situ cross-linked collagen fibers threedays after electrospinning with no water treatment.

FIG. 25B is an SEM image of in-situ cross-linked collagen fibers threedays after electrospinning with no water treatment

FIG. 25C is an SEM image of in-situ cross-linked collagen fibersprovided with a water treatment three days after electrospinning

FIG. 25D is an SEM image of in-situ cross-linked collagen fibersprovided with a water treatment three days after electrospinning.

FIG. 26 is a graph illustrating the relationship between stress andstrain for post-cross-linked collagen and in-situ cross-linked collagenin a dry state.

FIG. 27 is a chart illustrating the relationship between stress andstrain for in-situ cross-linked collagen in a hydrated state.

FIG. 28 is a FTIR spectrum of water treated in-situ cross-linkedcollagen membranes.

DETAILED DESCRIPTION

The apparatuses and methods disclosed in this document are described indetail by way of examples and with reference to the figures. It will beappreciated that modifications to disclosed and described examples,arrangements, configurations, components, elements, apparatuses,methods, materials, etc. can be made and may be desired for a specificapplication. In this disclosure, any identification of specific shapes,materials, techniques, arrangements, etc. are either related to aspecific example presented or are merely a general description of such ashape, material, technique, arrangement, etc. Identifications ofspecific details or examples are not intended to be and should not beconstrued as mandatory or limiting unless specifically designated assuch. Selected examples of apparatuses and methods for formingbiocompatible protein structures from a solution of protein dissolved ina benign solvent and cross-linking such protein structures arehereinafter disclosed and described in detail with reference made toFIGS. 1-28.

Naturally occurring materials are good candidates for products anddevices that are intended for use with biological material such as humanand animal tissue. One category of materials that can be compatible withthe biological material is natural polymers such as proteins. Examplesof such biocompatible proteins include, but are not limited to,collagens, gelatin, elastin, fibrinogen, silk, and other suitableproteins. Such proteins can be used to form protein structures forimplantation into or application onto a human body. Other materials thatare generally biocompatible are polysaccharides such as hyaluronic acid,chitosan, and derivatives of starch and cellulose such as hydroxypropylmethyl cellulose phthalate, deoxyribonucleic acid (DNA), and ribonucleicacid (RNA).

One example of a protein structure that can be useful in formingproducts and devices for the human body is a scaffold or porous matformed from protein fibers. Protein fibers can be used to construct ascaffold or porous mat structure that mimics an extra cellular matrix(ECM) of human tissue. Natural ECM generally has an open and porousstructure. As will be described herein, fibers formed from proteins andjoined into a matrix can simulate such an open and porous structure.Such a protein structure can be used in tissue engineering or wound careas a substrate for growing cells and/or tissue.

In another example, proteins can be used to form structures such as, forexample, generally spherical agglomerates. Such agglomerates can beformed in a variety of sizes, ranging from submicron diameters toseveral hundred micrometers in diameter. Because of the compatibility ofproteins with human tissue, protein agglomerates can be successfullyimplanted in or passed through the human body to affect treatment of amedical condition. For example, protein agglomerates can function as acomponent in a drug delivery system. A drug or other useful chemicalcompound can be attached to or inserted into a protein agglomerate. Theprotein agglomerate can then be passed through the human body, includingthrough the blood stream, to a desired location where the drug can bereleased. In another example, protein agglomerates can function asstructural or supportive components in the human body. For instance,protein agglomerates can be used in cosmetic medicine. Proteinagglomerates can be injected under the skin to support the skin andsmooth out wrinkles.

One method of forming a protein structure begins with dissolving aprotein such as collagen in a solvent. Once dissolved, the protein canbe extracted from the solvent and organized into a protein structure.One common solvent is 1,1,1,3,3,3 hexafluoro-2-propanol (HFP). However,any protein structure produced using such a solvent can have limitedusefulness because of health concerns. For example, the United StatesFood and Drug Administration (FDA) has strict guidelines as to theamount of HFP allowed in a device or product intended for use with thehuman body. Because of strict FDA guidelines and general healthconcerns, using a solvent with benign characteristics for dissolvingproteins or other biocompatible materials can yield biocompatiblestructures for implantation into or application onto a human body.Generally, a benign solvent is a solvent that either reduces healthrisks to a human body or is of minimal risk to the health of a humanbody.

One example of a benign solvent for dissolving protein comprises water,alcohol, and salt. The protein can be a Type I collagen, the alcohol canbe ethanol, and the salt can be sodium chloride (NaCl). The associationbetween water molecules, salt, and alcohol creates a complex structurein which proteins such as collagen are substantially soluble. Collagenis insoluble in most solvents because of interpeptide interaction.Collagen is substantially soluble in suitable water-alcohol-salt benignsolvents because the properties of the solvents screen interpeptideinteraction that usually results in insolubility of collagen. Forexample, the electrostatic interaction between the salt and the carbonylgroup of the hydrophilic part of collagen and the hydrophobicinteraction between the hydrocarbon chain of ethanol and the hydrophobicpart of collagen can screen such interpeptide interaction. In general,any molecule or complex that exhibits a hydrophilic part and ahydrophobic part spaced by approximately the same distance as thehydrophilic part and hydrophobic part of the collagen molecule candissolve collagen.

Although examples described herein include Type I collagen, it will beunderstood that all collagens—Type II, Type III, and so on—can be usedin forming a protein structure for use with human tissue.

Generally, in suitable water-alcohol-salt solvents, the ratio of waterto alcohol can range from a volume ratio of about 99:1 to about 1:99,the salt concentration can range from near 0 moles per liter (M) to themaximum salt concentration soluble in water, and the amount of proteinby weight (as compared to the solvent) can range from near 0 percent toabout 25 percent. In one example, the benign solvent comprises about aone-to-one ratio of water to ethanol and a salt concentration of about 3M NaCl. Collagen is dissolved in such a solvent until the solutionreaches about 16 percent collagen by weight. In another example, thesolution comprises semed S (principally collagen type I with a ca. 5percent collagen type III) dissolved in a solvent comprising phosphatebuffered saline (PBS) buffer and ethanol, where the buffer to ethanolratio of about one-to-one by volume. The saline concentration in the PBSbuffer can range from 5× to 20×. The collagen concentration can be forexample about 16 percent as compared to the total weight of thePBS/ethanol solvent. In yet another example, the protein dissolved inthe solvent can be gelatin. The solvent can comprise a PBS buffer with asalt concentration of 10× mixed with ethanol at a one-to-one ratio byvolume. Gelatin can be dissolved until the amount of gelatin by weightis about 16 percent by weight.

When protein has been dissolved in a suitable water-alcohol-salt solventto form a protein solution, suitable processing methods can be used toextract protein from the solution and form protein structures. Aspreviously discussed, such protein structures can be implanted into orapplied onto the human body to affect treatment of a condition. Examplesof suitable processing methods include, but are not limited to,electrospinning, electrospraying, and gravitational feed methods.

In one example, electrospinning can be used to form a protein structure.An example of apparatus 10 for forming a protein structure byelectrospinning protein dissolved in a benign water-alcohol-saltsolution is schematically shown in FIG. 1. The electrospinning methodcan include placing the protein solution in a syringe 12. The syringecan include a metal needle 14. The protein solution in the syringe 12can be charged by the application of an electrical potential between themetal needle 14 and a ground target 16 spaced a distance away from themetal needle 14. The electrical potential can be applied by charging themetal needle 14 with a voltage from a power supply 18. The electricalpotential can be increased until the electrostatic forces in the proteinsolution overcome the surface tension at the tip of the metal needle 14.As this surface tension is overcome, a fine jet 20 of solutioncontaining entangled protein chains can be drawn out of the metal needle14. As the fine jet 20 travels through the air, at least a portion ofthe solvent evaporates, resulting in a protein fiber 22 that dries as ittravels through the air. The dry protein fiber 22 can be collected on asurface 24 that is in contact with the ground target 16. As shown inFIG. 1, the surface 24 can be on a rotating cylinder 26. It will beunderstood that the electrical potential can be created using a directcurrent (DC) power supply or an alternating current (AC) power supply.

In one example, the protein solution can be placed in a 5 milliliter(ml) syringe equipped with a 21 gauge blunt needle. The syringe can beplaced in a syringe pump. A rotating drum can be placed approximately 10centimeters (cm) from the tip of the needle. The pump rate can be set toabout 1 milliliter per hour (ml/h) and the electrical potential can beset to about 20 kilovolts (kV). The result of such a setup can includethe formation of a scaffold or mat on the rotating drum containingrandomly oriented fibers or quasi-aligned fibers. The electrospinningprocess parameters, such as flow rate, potential field, andneedle-to-collector distance can be adjusted to produce a variety ofresults or to optimize the stability of the fine jet of solution duringelectrospinning.

In another example, a scaffold or mat can be electrospun from a solutionof about 16 percent by weight of gelatin dissolved in a PBS (10×) andethanol solution with a volume ratio of about one-to-one. A flow rate ofabout 1 ml/h, a potential field of about 20 kV, and aneedle-to-collector distance of about 10 cm can produce a stable jet ofgelatin drawn from the gelatin solution.

Electrospinning proteins such as collagen and gelatin can result in thespinning of fibers as shown in FIG. 1. Such fibers can be highly alignedor oriented when mats and scaffolds are formed. In one example,electrospinning may be used to draw out protein fibers and such fiberscan be generally arranged in a matrix. Once the fibers are arranged in amatrix, the fibers can be cross-linked to mimic the structure of ECM.Once cross-linked, the formed mat or scaffold can be a stablenon-water-soluble protein structure that is biocompatible with the humanbody and thus implantable into or applicable onto the human body.

As the mat or scaffold is being formed by electrospinning, the fiberscan be arranged so that fibers overlay one another and are in contactwith one another. While in such an arrangement, the physical structureof the mat or scaffold can be enhanced by cross-linking the proteinfibers. In one example, end groups such as aldehyde, carbodiimide, orepoxy can facilitate the cross-linking of the protein fibers of the mator scaffold. A carbodiimide such as EDC can cross-link collagen usingNHS as a catalyst. An electrospun collagen mat can be immersed in a 200mM EDC and NHS ethanol solution for approximately 4 hours to cross-linkcollagen fibers. Once cross-linked, the collagen mat or scaffold can beplaced in a PBS and salt solution similar to the buffer described above.Such a step can remove any non-cross-linked collagen from the mat orscaffold. The mat and scaffold, which can mimic the extra cellularmatrix of human tissue can now be used as a substrate to grow cells ortissue, or can be used as a covering for an open wound to promote growthof tissue of the wound.

Examples of methods for forming a protein mat or scaffold byelectrospinning can include adjusting the protein's solubility in thebenign solvent; adjusting the evaporation rate of the solvent; adjustingthe viscosity of the solution; or adjusting the surface tension of thesolution. In one example, the solubility of collagen is enhanced by theaddition of a salt to a water and ethanol mixture with a generallyneutral pH level. When about 5 percent by weight of NaCl is added to awater and ethanol mixture for an about 16 percent by weight collagensolution, substantially all collagen dissolves. In one example, the saltcomposition of a PBS buffer solution can be about 80 percent NaCl byweight, about 17.4 percent sodium phosphate anhydrate by weight, andabout 2.4 percent potassium phosphate anhydrate by weight. In anotherexample, collagen may be dissolved in a PBS buffer where the total saltconcentration exceeds 5 percent by weight. The evaporation rate of thesolvent can be increased by increasing the amount of alcohol as comparedto water in the protein solution.

As will be understood, the pH level, temperature, type of collagen, andtype and concentration of salt all influence the structure of collagenin the protein solution. For example, at low collagen concentrations anda pH level of about 7.4, the transition temperature of crystallinepolymer to random coil polymer is about 45 degrees Celsius. Thetransition temperature can be independent of salt concentration forpotassium chloride (KCl) and NaCl. There is a progressive decrease inprecipitation of collagen, that is to say that collagen becomes moresoluble as more salt is added. Addition of salt results indestabilization of the precipitated collagen while the ionic strengthincreases with salt additions. Collagen solubility can increase even ifit appears that the crystalline structure of collagen is maintained uponaddition of salt.

Alcohol affects the solubility of collagen in the buffer and ethanolsolution. Alcohol and collagen interaction is moderated by hydrocarbonchain length, with alcohol disrupting internal hydrophobic interactionsin the collagen. With increased alcohol concentration, there is aprogressive increase in molar destabilization of the crystallinecollagen precipitated in an alcohol and potassium acetate buffer mixtureat an acidic pH, for example, a pH of about 4.8. For single collagenmolecules, structural stability is primarily a function of interpeptidehydrogen bonding and chain rigidity.

The addition of salt promotes the solubility of collagens. Hydrogenbonding between the hydrophilic part of collagen and water molecules canbe too weak to break the interpeptide interaction, and the strongerelectrostatic forces induced by salt in aqueous media may be necessary.The combination of both electrostatic and hydrophobic forces appears tointeract strongly enough with the collagen chain to substantiallydissolve the collagen in a mixture of ethanol and PBS buffer with anabout one-to-one ratio when a salt concentration is at least about 5× inthe buffer.

In addition to dissolving proteins such as collagens, the buffer andethanol binary solvent can further facilitate the electrospinningprocess. The salt in the buffer as well as the alcohol can assists inovercoming the high surface tension of water that can partially inhibitspinnability of water based polymeric solution. In addition, the saltincreases the charge density in the protein solution, which canfacilitate the formation of a stable Taylor cone. The low evaporationrate of water, which can inhibit the formation of fibers duringelectrospinning, can be compensated for by the high evaporation rate ofalcohol.

Electrospinning of collagen solutions with about a one-to-one volumeratio of ethanol to PBS (10× or 20×) can be stable and create fiber matsor scaffolds that exhibit relatively consistent fiber diameters. Theincrease of salt concentration in the PBS buffer can decrease the fiberdiameter, and higher salt concentration can result in greater elongationof the electrospun jet due to higher density of repulsive charges in theTaylor cone. As is shown in the chart of FIG. 2A, increasing the saltconcentration from 10× to 20× decreases the average fiber diameter from540 micrometers to 210 micrometers but also significantly reduces thestandard deviation of the fiber diameter distribution (from 210micrometers to 60 micrometers). FIG. 2B is a scanning electronmicroscope (SEM) image of collagen fibers electrospun from PBS (20×) andethanol.

As will be understood, cross-linking of protein mats or scaffoldsfacilitates the use of electrospun mats or scaffolds for regenerative ortissue engineering and wound care, because cross-linking promotesstability of the collagen mat or scaffold. In addition to mimicking theECM of human tissue to promote cell or tissue growth, when collagenswith hemostatic properties are used, application of a mat or scaffoldover a new or existing wound can arrest blood flow from the wound andpromote clotting.

Cross-linking can be facilitated by the presence of carboxyl groups onthe hydrophilic part of collagens. FIGS. 3A and 3B illustratecross-linking of fiber mats with EDC and NHS as a catalyst. Mats areimmersed in an ethanol solution comprising EDC and NHS for four hours.The mats can then be immersed in a buffer solution containing the samesalt concentration as the one the collagen was electrospun from toremove un-cross-linked fibers.

For the collagen mats shown in FIGS. 3A and 3B, the collagen fibers ofthe mat were cross-linked with EDC and NHS. The fibers were electrospunfrom a PBS (10×) and ethanol solution. FIG. 3A is an SEM image of aself-standing mat and FIG. 3B is a framed mat. FIG. 3C is a chart of thediameter distribution of cross-linked fibers electrospun from a PBS(10×) and ethanol mixture. As seen in FIG. 3B, the cross-linked mat mayretain a porous and open structure upon cross-linking.

A collagen mat can be soaked in an ethanol solution such that the matshrinks to form a film-like surface (for example, as shown in FIG. 3A).If shrinkage is not desired, frames can be placed on each side of themat and clipped together to prevent the mat from shrinking when it isimmersed in the ethanol solution (for example, as shown in FIG. 3B).Such frames can be constructed of material that is easy to remove, suchas Teflon. The fiber diameter distribution does not significantly changebetween non-cross-linked and cross-linked collagen when a frame is used.Therefore, the frame can efficiently prevent fiber shrinkage whenimmersed in ethanol.

The architectural structure of protein mats or scaffolds can beimportant depending on the intended application of the mat or scaffold.For example, mats and scaffolds can be used to simulate types of humantissue. Aligned fibers may be useful in simulating a variety of tissuetypes including ligaments, nerves, cardiac tissues, and the like. Thealignment of electrospun fibers may be controlled by the rotationalspeed of the rotating cylinder 26 shown in FIG. 1. If the speed of thecylinder matches or is faster than the speed of the jet of proteinsolution exiting the syringe, the protein fibers may be drawn out of thesyringe in the loop direction of the cylinder. The orientation ofprotein fibers in the mat can be characterized by Herman's orientationfunction, which is:f=(3*(cos² θ)−1)/2where θ is the angle of the protein fibers compared to the loopdirection of the drum.

An optimally aligned fiber mat (that is to say, a mat where all thefibers all aligned in the same direction) will have a Herman'sorientation function equal to 1. An optimally random configured fibermat (that is to say, a mat where all the fibers are randomly aligned)will have a Herman's orientation function equal to −0.5. FIG. 4A showsan SEM image of a protein fiber mat, where the speed of the rotatingdrum matched the speed of the jet of protein solution. The mat waselectrospun from a PBS (20×) and ethanol solution and has a Herman'sorientation function equal to about 0.93. The mat shown has relativelyhighly oriented fibers. Because oriented fibers can be mechanicallydrawn, the fibers can have smaller diameters than randomly orientedfibers electrospun under similar conditions. However, as shown in FIG.4B, for this particular mat, where the speed of the rotating drummatched the speed of the jet of protein solution, the drawn and alignedfibers do not show significantly smaller diameters than random fibers.

As previously discussed, gelatin may be electrospun from binarysolutions and electrospinning conditions disclosed herein. For example,when a PBS (10×) and ethanol solution is used for dissolving gelatin atabout 16 percent by weight, similar results are obtained as compared tocollagen fibers. In addition, the gelatin can be cross-linked in asimilar manner and under similar conditions as described for collagens.FIG. 5A shows a gelatin fiber mat and FIG. 5B shows a chart of thediameter distribution of the gelatin fibers.

The concentration of collagen in the solution may affectelectrospinning. Collagens readily dissolve in a solvent comprising aone-to-one ratio between PBS (20×) and ethanol. Generally, collagensolutions ranging from about 4 percent by weight to about 25 percent byweight can be electrospun. By controlling the concentration of collagen,different morphologies and fiber diameters can result. FIG. 6 includesseveral SEM images of morphologies resulting from electrospinningdifferent concentrations of collagen dissolved in solutions. FIGS. 6 aand 6 b are different magnifications of a fiber mat electrospun from asolution with about 4 percent collagen by weight. As may be seen,generally the diameter of the fibers is inconsistent because theviscosity of the solution is low and does not generally form continuousfibers during electrospinning. FIGS. 6 c and 6 d are differentmagnifications of a fiber mat electrospun from a solution with about 10percent collagen by weight. As the concentration of collagen isincreased, the diameter of the fibers becomes more consistent becausecontinuous fibers are more readily generated by a solution with about 10percent collagen by weight. FIGS. 6 e and 6 f are differentmagnifications of a fiber mat electrospun from a solution with about 16percent collagen by weight. As can be seen, submicron fibers ofgenerally consistent diameter are formed.

The concentration of salt and ethanol can affect the solubility ofcollagens in water. Collagen can be generally insoluble at about 16percent by weight in either PBS (20×) or ethanol. However, when a smallamount of ethanol is added into PBS (20×) buffer to form a PBS (20×) toethanol volume ratio of about nine-to-one, the collagen substantiallydissolves into this mixture. By adding more ethanol into PBS (20×)buffer (that is, the volume ratio decreases from about nine-to-one toabout seven-to-three to about one-to-one) there is generally no affecton the solubility of collagen. The collagen remains substantiallysoluble. However, when the PBS (20×) to ethanol volume ratio is reducedto three-to-seven, collagen is generally no longer soluble. Furthermore,the salt concentration affects the solubility of collagen when the waterto ethanol volume ratio is held constant at about one-to-one. The saltconcentration in 5×, 10× and 20×PBS buffer is sufficient tosubstantially dissolve collagen in the mixture solution.

The addition of salt and ethanol to the protein solution can facilitatethe electrospinning of the polymer solution. As salt increases theconductivity and ethanol decreases the boiling point, concentrations ofsalt and ethanol affect the electrospinnability of solutions that arecapable of dissolving collagen with PBS (20×) to ethanol ratio varyingfrom about nine-to-one to about one-to-one. As seen in FIGS. 7 a-7 b,fibers may be formed from electrospinning collagen with PBS (20×) toethanol volume ratios of about seven-to-three. In addition, collagensolutions with a PBS (20×) to ethanol volume ratio of about one-to-onedemonstrate good electrospinability and a stable Taylor cone. Such asolution may be electrospun to form fibers and a mat as thick as about150 microns.

In one example, the protein solution can include a cross-linking agentso that cross-linking of protein fibers occurs as the protein fibers arebeing electrospun. This reduces the formation and cross-linking ofprotein fibers to one general step. In such an example, the proteinsolution includes protein, water, alcohol, salt, and a cross-linkingagent. A protein solution is formed by dissolving about 16 percent byweight of collagen in a solvent. The solvent comprises PBS buffer (20×)and alcohol. Prior to forming the solvent a cross-linker is added to thealcohol. The cross-linker can be about 200 mMoles of EDC and NHS at aratio by weight of about one-to-one. The collagen solution can bedeposited in a syringe equipped with a metal needle as previouslydescribed. The protein solution is subjected to an electrical potentialand electrospun to form a jet of protein solution and form a proteinstructure such as a mat or scaffold. In one example, a voltage of about20 KV can be applied to the metal needle and the pump rate can be about0.5 milliliters per hour. A rotating drum can be positioned about 10centimeters from the needle to collect the electrospun mat.

Protein dissolved in benign solvents as described herein can be used toform protein agglomerates such as generally spherical particles orbeads. An apparatus 100 for forming protein agglomerate is schematicallyshown in FIG. 8. Protein agglomerates can be formed using methods thatinclude electrospinning, electrospraying, and gravitational feedmethods. The apparatus 100 includes a syringe 102 equipped with a metalneedle 104. The syringe 102 is suspended over a receptacle 106, and thereceptacle 106 is positioned on a metal plate 108, which is grounded. Aprotein solution comprising protein dissolved in a water-alcohol-saltsolvent as described herein is placed in the syringe 102. Similar toprevious descriptions, an electrical potential can be applied to chargethe protein solution by applying a voltage from a power supply 110 tothe metal needle 104. A solution of a cross-linking agent such as EDCdissolved in a solvent such as ethanol can be placed in the receptacle106.

For electrospinning, the electrical potential can be increased to growthe electrostatic forces and overcome the surface tension at a tip ofthe needle 104. As this surface tension is overcome, a fine jet ofprotein solution containing entangled protein chains can be drawn out ofthe needle 104. As the fine jet travels through the air, the solventevaporates leaving a dry protein fiber that engages the surface of thecross-linking solution in the receptacle 106. The impact of the proteinfiber's engagement with the surface of the cross-lining solutionfractures the fiber into relatively short sections. Upon entering thecross-linking solutions, each short section of protein fiber drawsinward and cross-links with itself, resulting in a generally sphericalprotein agglomerate or bead. In one example, the protein solventcomprises about 16 percent collagen by weight dissolved in a solvent ofabout one-to-one ratio by volume of PBS buffer (20×) to ethanol. A flowrate of about 1 ml/h is applied to the protein solution in the syringe102, a voltage of about 25 kV is applied to the metal needle 104, andthe metal plate 108 is spaced about 20 cm from the tip of the metalneedle 104. An cross-linking solution of EDC dissolved in ethanol isplaced in the receptacle 106. Such parameters form cross-linked proteinagglomerates as shown in FIG. 9. Such protein agglomerates can be, forexample, more than 100 micrometers in diameter.

For electrospraying, the tip of the needle 104 and the grounded plate108 can be placed closer together as compared to the describedelectrospinning method. Such positioning can result in the proteinsolution exiting the needle 104 and forming droplets of solution priorto entering the cross-linking solution in the receptacle 106. Suchdroplets internally cross-link once entering the cross-linking solutionand form spherical protein agglomerates or beads. Protein agglomeratesformed by electrospraying are shown in FIG. 10. Such proteinagglomerates can be, for example, approximately 2 to 3 micrometers indiameter.

For a gravitation feed method, no electrical potential is needed.Gravity is used to draw beads of protein solution from the needle 104.The beads fall into the cross-linking solution and internally cross-linkforming generally spherical protein agglomerates. Alternatively, eachbead can break up into smaller beads upon impact with the surface of thecross-linking solution. Protein agglomerates formed by the gravitationalfeed method are shown in FIG. 11. Such protein agglomerates can be, forexample, approximately 20 to 30 micrometers in diameter.

Parameters such as the distance between the tip of the needle 104 andthe metal plate 108, flow rate of protein solution from the needle 104,voltage applied to the needle 104, concentration of protein in theprotein solution, concentration of salt in the protein solution, andratio of alcohol to water in the protein solution can affect the size ofprotein agglomerates or beads. However, for comparatively similarparameters, electrospraying can produce the smallest proteinagglomerates, gravity feed can produce protein agglomerates larger thanelectrospraying, and electrospinning can produce protein agglomerateslarger than the gravitational feed method.

Protein dissolved in benign solvents as described herein can be used toform porous protein films, scaffolds and gels. In one example, a proteinsolution can be deposited in a receptacle so that the protein solutioncovers the bottom of the receptacle. A solution that includes across-linking agent such as EDC in ethanol is poured over the proteinsolution. In one example, the cross-linking solution comprises about 0.2millimoles of EDC. The receptacle can be hermetically covered for aperiod of time, for example about 24 hours. Evaporation of the solutionresults in a protein film forming on the bottom of the receptacle. Somesalt crystals may be present on the surface of the film. Such saltcrystals can be removed by washing the film with deionized water, whichcan leach out the salt. Once the salt is leached out, the film is leftwith a porous structure that includes numerous pores that intersectforming a protein structure with an open network of pores. FIGS. 12A and12B show porous films formed from the described method. The porousstructure of the film can include pores that range from submicron insize to over 30 micrometers in size.

Such a film with intersection pores can be suitable as a scaffold forcell repopulation or tissue growth. It will be understood that theintersecting pores mimic the ECM structure of human tissue and provideexpanded surfaces on which cells and tissue can grow.

An example of another method of forming a protein structure with an opennetwork of pores is hereafter described. A protein solution as describedherein is prepared in a receptacle and stirred. As the protein solutionis stirred, a cross-linking solution including a cross-linking agentsuch as EDC is deposited in the receptacle. Stirring continues until aprotein cross-links and forms a gel in the receptacle. Once cross-linkedthe protein gel can be rinsed with deionized water to remove salts andalcohol from the gel. The gel is quenched in liquid nitrogen and frozen.The gel is placed in a vacuum chamber and water in or on the gelsublimes or otherwise evaporates. Such a method results in a low densityprotein scaffold with foam-like properties and an open network of pores.FIGS. 13A and 13B show a scaffold with an open network of pores formedfrom the described method. The pores as shown range in size from about10 micrometers to about 50 micrometers. The size of the pores can becontrolled by varying the protein content in the protein solution andthe buffer to alcohol ratios.

Additional methods of forming cross-linked protein structures can beachieved by combining the formation of protein fibers and a delayedpost-cross-linking treatment in a single step. In one example, a methodof forming cross-linked proteins is an in-situ method of kineticallycontrolling cross-linking resulting in versatile processing of collagenand other proteins. This is to say that the formation of protein fibersis achieved such that a cross-linking process of the fibers is delayed.Such a method enables protein fibers to cross-link after the formationof such fibers, without the need for a post-production process. Suchversatility in processing provides for methods that can be designed toproduce structures, products, devices, etc. for specific purposes.

One such method includes adding NHS and EDC to solutions of proteindissolved in ethanol and PBS. The time it takes for a cross-linkingprotein solution to become hydrogel (i.e., gelation time (t_(gel))) canbe dependent on the mole ratio of NHS to EDC. Gelation time can bedefined as the time at which the shear storage (G′) and loss (G″) moduliare approximately equal. The shear storage and loss moduli can bedetermined rheologically in dynamic oscillatory shear experiments.Gelation time as a function of mole ratios of NHS to EDC can bedetermined by using an AR-2000ex Rheometer. FIG. 14A illustrates therelationship between gelation time and mole ratio of NHS to EDC based onrheological results, where the concentration of EDC is fixed at 200 mM.FIG. 14B illustrates the relationship between the log of gelation timeand mole ratio of NHS to EDC based on rheological results. As is shownin FIGS. 14A and 14B, the gelation time shows a substantial increasebeginning at a NHS/EDC ratio of 1.5, with a generally linearrelationship with NHS/EDC molar ratios of two-to-one or greater thantwo-to-one. For NHS/EDC mole ratios below two-to-one, protein solutionsbecome gel relatively quickly. The addition of excess NHS (i.e.,increasing the NHS to EDC ratio) can postpone or delay the cross-linkingreactions.

In one example, increasing the ratio of NHS to EDC can increase thedelay in cross-linking reactions from minutes to two to three hours ormore. Such a delay can be used to control cross-linking by delaying thecross-linking so as to provide for the versatile processing of proteinssuch as collagen. During such a delay in cross-linking, the solution ofprotein dissolved in a benign solvent can be processed into a variety ofshapes and morphologies. For example, electrospinning of protein fibersfrom the benign solvent became possible, with crosslinking occurringin-situ afterward.

In one example a collagen hydrogel can be formed using the followingmethod. A collagen solution can be formed by dissolving about 16 percentby weight of collagen in a solvent such as PBS buffer (20×) and alcoholwith volume ratio of about one to one. Optionally, prior to adding thebuffer, a bio-friendly cross-linker can be added to the alcohol. Thecross-linker can be about 200 mM of EDC and 400 mM of NHS. Across-linked collagen hydrogel can be formed in about 2 hours. Thecollagen hydrogel can be rinsing in water to remove alcohol and saltsafter gel formation. FIGS. 15A and 15B depict collagen hydrogel formedat least partially by the foregoing method. FIG. 15A depicts hydratedcollagen gel, and FIG. 15B depicts lyophilized collagen gel.

Collagen foam can be formed by lyophilizing the in-situ cross-linkedhydrogel. Such a lyophilized collagen gel can have a sponge-likestructure that can include pore sizes ranging from approximately severalmicrons to approximately several tens of microns. FIG. 16A is a scanningelectron microscope (SEM) image of a cross section of lyophilizedin-situ cross-linked collagen gel; FIG. 16B is an SEM image of a topportion of FIG. 16A; FIG. 16C is an SEM image of a middle portion ofFIG. 16A; and FIG. 16D is an SEM image of a bottom portion of FIG. 16A.Such a collagen porous structure can benefit cell culturing andproliferation. Such a collagen porous structure can also improvecollagen gel performance in tissue engineering.

Collagen gels can be fabricated in different shapes, sizes andconfigurations. In one example, collagen hydrogel can be fabricated as atube-like structure. One method of forming such a tube-like collagenhydrogel is to pour or otherwise deposit the above-described collagensolution into a mold prior to the onset of gelation. As shown in FIG.17A, collagen hydrogels can be formed into tube-like structures ofvarying lengths and thicknesses. The structures shown in FIG. 17A areimmersed in water. In another example, collagen gels can be fabricatedas a hemispheric-like structure via in-situ cross-linking methods. Sucha hemispheric-like structure is shown in FIG. 17B. The structure shownin FIG. 17B is immersed in water. Such a hemispheric-like structure canbe applicable in the field of ocular medication. For example, collagengels can be fabricated as a contact lens-like shaped structure.

Furthermore, before the onset of gelation the collagen hydrogel canstill be liquid-like in nature. In such a liquid-like state, collagenhydrogel can be used for a number of different procedures such as, forexample, printing or coating. The collagen hydrogel can be used as an“ink” that is used to print on a glass slide. As shown in FIG. 18,collagen hydrogel can be useful as an “ink” to print on a glass slide.

In another example, drugs or medications can be incorporated intocollagen gels for sustained drug delivery. Various drugs can be loadedinto the collagen solution prior to cross-linking so as to entrap orembed the drug after gel formation. In addition to drugs andmedications, many polymeric materials can be entrapped or embedded intothe collagen gel. Many different drugs can be loaded into embeddedpolymer materials and/or collagen gel. The drugs can be releasedsimultaneously with tunable release profiles. In one example,electrospun poly(caprolactone) (PCL) containing photodynamic therapydrug Pc4 and electrosprayed PLGA macrobeads with beta-carotene can besuccessfully embedded into in-situ cross-linked collagen hydrogels. Suchan arrangement is shown in FIGS. 19A and 19B. FIG. 19A depicts in-situcross-linked collagen hydrogels with PCL-Pc4 mat embedding. FIG. 19Bdepicts in-situ cross-linked collagen hydrogels with PLGA-beta carotenemacrobeads. The collagen hydrogel samples of both FIG. 19A and FIG. 19Bare immersed in water.

The delay in cross-linking reactions due to NHS/EDC ratios provides aperiod of time for a number of processes prior to the collagen becomingcross-linked. Such a delay provides for a variety of methods thatincorporate additional processing during the formation of collagenhydrogels. The incorporation of addition processing allows for collagenhydrogels to be designed to serve any number of functions and purposes.

In one example, an electrospun in-situ cross-linked collagen fibrousscaffold can be fabricated by using electrospinning techniques. Suchtechniques can begin with a benign solvent. In one example, a collagensolution can be prepared by dissolving about 16 percent by weight ofType I collagen in a solvent such as PBS buffer (20×) and alcohol withvolume ratio of about one to one. Prior to adding the buffer, thecrosslinker can optionally be added to the alcohol. The crosslinker canbe, for example, about 400 mM of NHS and about 200 mM of EDC.

As similar described with regard to FIG. 1, the mixed collagen solutioncan be loaded to a 5 ml BD syringe with a 21 gauge blunt needle, whichcan then be placed in a syringe pump. The process parameters (such asflow rate, potential field, and needle-collector distance) can be variedto optimize the stability of the electrostatic jet. Electrospinning canbe carried out at 20 KV with a pump rate of 0.5 ml/h. A drum rotating at5 m/s is placed 12 cm far from the needle in order to collect theelectrospun fibers. Electrospun collagen fibrous scaffolds fabricatedwith such a process are shown in FIGS. 20A and 20B. FIG. 20A depicts anelectrospun in-situ cross-linked collagen fibrous scaffold in a drystate. FIG. 20B depicts an electrospun in-situ cross-linked collagenfibrous scaffold in a hydrated state immersed in water.

Such an in-situ cross-linking electrospinning method can generategenerally cylindrical and continuous collagen nanofibers in randomarrays with a generally porous structure. FIGS. 21A and 21B depict suchelectrospun in-situ cross-linked collagen fibers at two differentmagnifications. FIG. 21C is a histogram of the diameter of electrospunin-situ cross-linked collagen fibers, and FIG. 21D is a chart of averagefiber diameter and a function electrospinning time. The average fiberdiameter is approximately 0.42±0.11 micrometers. The diameter of in-situcross-linked collagen fibers increased from 0.35 to 0.46 micrometersduring approximately three hours of electrospinning (as shown in FIG.21D), which suggests that the onset of cross-linking occurs during thattime. The average fiber diameter of 0.42 micrometers is about twice thediameter of collagen fibers generated from ethanol/PBS withoutcross-linking. The addition of EDC into the collagen solution canincreased the viscosity, even though macroscopic gelation was postponedby the presence of excess amount of NHS. A higher viscosity of collagensolution can result in the formation of larger fibers. Similar resultswere also found in rheological experiments. During testing the storagemodulus (G′) of in-situ crosslinking collagen solution increased untilthe dynamic oscillatory shear testing finished, which indicates that theviscosity of solution gradually increased after mixing the collagen andthe crosslinkers together.

Humidity levels can be an important in-situ cross-linked collagennanofiber scaffolds were tested at relative humidities of 33%, 43% and53% at room temperature. SEM images of electrospun, in-situ crosslinkedcollagen fibers tested at these different humidity levels for certainperiods of time are shown in FIGS. 22A-C. FIG. 22A depicts a collagenfiber scaffold stored at 33% humidity for three days. FIG. 22B depicts acollagen fiber scaffold stored at 43% humidity for three days. FIG. 22Cdepicts a collagen fiber scaffold stored at 53% humidity for 1 day. Asis shown, relative humidity can be an important parameter to control thefiber morphology of in-situ cross-linked collagen after electrospinning.A collagen fiber scaffold stored at 33% humidity for three days (FIG.22A) includes individual fiber features. A collagen fiber scaffoldstored at 53% for one day (FIG. 22C) includes some melting of fibers. Ahigher humidity can plasticize the collagen before extensivecrosslinking by incorporated EDC and NHS, while lower humidity may limitthe motilities of the crosslinkers and collagen chains in the fibers.

Post-crosslinking of collagen fiber scaffolds was also performed byimmersing the collagen scaffolds electrospun from ethanol/PBS withoutcrosslinkers into 200 mM each of EDC and NHS in ethanol for 4 hours.After the post-crosslinking process, the resulting collagen scaffoldsshrank to 40% of the original dimensions when immersed in the water, asshown in FIGS. 23A and 23B. In-situ cross-linked collagen scaffolds canswell up to two-fold of the original size when they were hydrated (seeFIGS. 20A and 20B). The water-treated, in-situ cross-linked collagenscaffolds include a porous structure, as shown in FIGS. 24A and 24B. EDCand NHS are more uniformly distributed in collagen fibers when using thein-situ method described herein and cross-linking reactions can occurthroughout the fibers, which can result in more homogeneouslycrosslinked collagen scaffolds.

Another example of a collagen fibrous scaffold that is relatively denseand water-insoluble obtained after electrospinning is depicted in FIGS.25A and 25B. The collagen fibrous scaffold depict was in-situcross-linked three days after electospinning and prior to any watertreatment. FIGS. 25A and 25B depict a relatively strong network with asignificant extent of interlinked fibers. Such a condition can be aresult of inter-molecular and intra-molecular covalent bonds and bondingbetween the fiber junctions. Using the methods disclosed herein, in-situcross-linked collagen scaffolds generally preserve their shape and alsoswell to some extent when hydrated (as shown in FIGS. 20A and 20B). Inaddition, the fibrous structure of in-situ cross-linked collagen matsproduced by the methods disclosed herein can largely be conserved afterwater-treatment. FIGS. 25C and 25D depict in-situ cross-linked collagenfibers three days after electospinning and after water treatment. Suchbehavior can be desirable and beneficial for cell culture and tissueengineering applications. The advantages of in-situ cross-linkedcollagen scaffolds as described herein can be ascribed to the efficiencyand homogeneity of cross-linking when EDC/NHS is incorporated within thefibers during electrospinning. With regard to post-cross-linking, thecross-linking reaction is mainly concentrated on the surface of collagenfibers because of the slow diffusion of EDC and NHS into the fibers,which is increasingly retarded as cross-linking continues at or near thesurface.

Uniaxial tensile stress tests of in-situ cross-linked collagen scaffoldswere performed on a dynamic mechanical analyzer (DMA-Q800, TAInstruments Inc.). Representative plots of the stress-strain curves ofdry scaffolds are shown in FIG. 26 and hydrated scaffolds in FIG. 27.Respective tensile properties in terms of peak stress, strain at break,and tangential modulus for dry scaffolds are summarized in Table 1below. The tensile results indicate that dry in-situ cross-linkedcollagen has greater peak stress and strain compared to those ofpost-cross-linked samples. Both high cross-link content and largelyfibrous texture of dry in-situ cross-linked collagen scaffolds can beresponsible for such differences.

TABLE 1 Tensile properties of post and in-situ cross-linked collagenmembranes Tangential Modulus Peak Stress (MPa) Strain at break (%) (MPa)In-situ cross- 14.53 ± 1.61 3.28 ± 0.12 654.29 ± 1.29 linked collagenPost cross- 11.33 ± 4.77 1.66 ± 0.09 778.40 ± 1.48 linked collagenFor hydrated in-situ cross-linked scaffolds, the peak stress is about0.22±0.02 MPa and strain at break is about 134.5±10.0 percent.

FTIR experiments have been conducted to explore the collagen innerstructure of electrospun in-situ cross-linked scaffolds. In a typicalFTIR spectrum of collagen, the amide I absorption arises predominantlyfrom protein amide C═O stretching vibrations, the amide II absorption ismade up of amide N—H bending vibrations and C—N stretching vibrations;the amide III peak is complex, consisting of components from C—Nstretching and N—H in plane bending from amide linkages, as well asabsorptions originating from wagging vibrations from CH₂ groups from theglycine backbone and proline side-chains. In FIG. 24, the indicativebands at 1653, 1541 and 1235 cm⁻¹, which are characteristic of the amideI, II and III absorptions, respectively, are the preliminary indicationthat the unique triple-helical structure of native collagen presents inthe in-situ cross-linked scaffolds. This result is also confirmed by thevalue of IR absorption ratio (0.86) between the 1235 (amide III) and1450 bands, which is larger than 0.59.

Regarding the mechanism of in-situ cross-linking by EDC/NHS, theamine-reactive O-acylisourea intermediate, which is formed by thereaction between EDC and carboxyl groups of collagen molecules, issusceptible to hydrolysis, making it unstable and short-lived in aqueoussolution. The addition of small amount of NHS can stabilize theamine-reactive intermediate by converting it to an amine-reactive NHSester, thus increasing the efficiency of EDC-mediated couplingreactions. The amine-reactive NHS ester can be more stable but lessactive than the amine-reactive EDC ester. Therefore, the addition ofexcess NHS can convert too many amine-reactive EDC esters to the lessactive NHS esters, which results in decreasing EDC activity and finallypostpones the full cross-linking reaction. Also, excess NHS can competewith amines for NHS esters, the former leading to “NHS exchange” anddelaying formation of amide bonds. The disclosed in-situ cross-linkingtechnique can also have applicability with other biomaterials includingpolypeptides and proteins and polysaccharides, to produce versatilestructures for tissue engineering.

Collagen and other protein-based gels can be formed by filling cavitiesof microfluidic devices followed by cross-linking. Such a method can beuseful for 3-D cell culturing. Also, the cross-linked gel can be removedfrom the device forming effectively a “microfluidically printed”structure.

The delayed cross-linking chemistry can be useful in functionalizingcollagen and other protein for later reactions different from thecarboxylic acid/amine coupling that occurs in the systems and methodsdescribed above. For example, it may be possible to functionalizecollagen with, for example, acrylates by reaction of methyl acrylate andcollagen amine units in the presence of EDC/NHS. The collagen could thenbe cross-linked later, for example by UV irradiation. One advantage isthe possibility of selective cross-linking depending upon which regionsare irradiated.

The foregoing description of examples has been presented for purposes ofillustration and description. It is not intended to be exhaustive orlimiting to the forms described. Numerous modifications are possible inlight of the above teachings. Some of those modifications have beendiscussed, and others will be understood by those skilled in the art.The examples were chosen and described in order to best illustrateprinciples of various examples as are suited to particular usescontemplated. The scope is, of course, not limited to the examples setforth herein, but can be employed in any number of applications andequivalent devices by those of ordinary skill in the art.

What is claimed is:
 1. A method of forming a cross-linked proteinstructure, comprising: forming a protein solution by dissolving aprotein in a solution of water, salt, alcohol, and a cross-linker,wherein the cross-linker is N-hydroxysuccinimide (“EDC”) and1-ethyl-3-(3-dimethylaminopropyl)carbodiimide hydrochloride (“NHS”), andthe protein is collagen; forming an intermediate protein structure fromthe protein solution; and after a period of time has elapsed,cross-linking at least a portion the intermediate protein structure toform the cross-linked protein structure.
 2. The method of claim 1,wherein the molar ratio of NHS to EDC is about 1:1.
 3. The method ofclaim 1, wherein the intermediate protein structure is formed by anelectrospinning process.
 4. The method of claim 1, wherein theintermediate protein structure is formed by an electrospraying process.5. The method of claim 1, wherein the intermediate protein structure isformed by a gravitational feed process.
 6. The method of claim 1,wherein the collagen dissolved in the solution is less than about 25percent by weight.
 7. The method of claim 6, wherein the collagendissolved in the solution is about 16 percent by weight.
 8. The methodof claim 1, wherein the cross-linker is EDC and NHS, and the protein isgelatin.
 9. The method of claim 8, wherein the molar ratio of NHS to EDCis 1:1.
 10. The method of claim 8, wherein the intermediate proteinstructure is formed by an electrospinning process.
 11. The method ofclaim 8, wherein the intermediate protein structure is formed by anelectrospraying process.
 12. The method of claim 8, wherein theintermediate protein structure is formed by a gravitational feedprocess.
 13. The method of claim 8, wherein the gelatin dissolved in thesolution is less than about 25 percent by weight.
 14. The method ofclaim 13, wherein the gelatin dissolved in the solution is about 16percent by weight.